Implantable stimulating assembly with limited components

ABSTRACT

An electric hearing prosthesis, wherein the electric hearing prosthesis includes an implantable portion configured to electrically stimulate a cochlea to evoke a hearing percept, and an external portion configured to be in wired communication with the implantable portion, wherein the electronic components of the implantable portion are all passive electronic components.

BACKGROUND

Hearing loss, which may be due to many different causes, is generally oftwo types: conductive and sensorineural. Sensorineural hearing loss isdue to the absence or destruction of the hair cells in the cochlea thattransduce sound signals into nerve impulses. Various hearing prosthesesare commercially available to provide individuals suffering fromsensorineural hearing loss with the ability to perceive sound. Oneexample of a hearing prosthesis is a cochlear implant.

Individuals suffering from hearing loss typically receive an acoustichearing aid. Conventional hearing aids rely on principles of airconduction to transmit acoustic signals to the cochlea. In particular, ahearing aid typically uses an arrangement positioned in the recipient'sear canal or on the outer ear to amplify a sound received by the outerear of the recipient. This amplified sound reaches the cochlea causingmotion of the perilymph and stimulation of the auditory nerve. Cases ofconductive hearing loss typically are treated by means of boneconduction hearing aids. In contrast to conventional hearing aids, thesedevices use a mechanical actuator that is coupled to the skull bone toapply the amplified sound.

In contrast to hearing aids, which rely primarily on the principles ofair conduction, certain types of hearing prostheses commonly referred toas cochlear implants convert a received sound into electricalstimulation. The electrical stimulation is applied to the cochlea, whichresults in the perception of the received sound.

It is noted that in at least some instances, there is utilitarian valueto fitting a hearing prosthesis to a particular recipient. In someexamples of some fitting regimes, there are methods which entail aclinician or some other professional presenting sounds to a recipient ofthe hearing prosthesis such that the hearing prosthesis evokes a hearingpercept. Information can be obtained from the recipient regarding thecharacter of the resulting hearing percept. Based on this information,the clinician can adjust or otherwise establish settings of the hearingprosthesis such that the hearing prosthesis operates according to thesesettings during normal use.

It is also noted that the electrode array of the cochlear implantgenerally shows utilitarian results if it is inserted in a cochlea.

SUMMARY

In accordance with an exemplary embodiment, there is a hearingprosthesis, comprising an electrode array of a cochlear implantconfigured to be implanted in a cochlea of a recipient, a lead assemblyextending from the electrode array, and a connector located at an end ofthe lead assembly opposite the electrode array, wherein the leadassembly is a percutaneous lead assembly, and the connector isconfigured to place the lead assembly into wired communication with anexternal stimulator of the hearing prosthesis.

In accordance with an exemplary embodiment, there is a system, there isan electric hearing prosthesis, comprising an implantable portionconfigured to electrically stimulate a cochlea to evoke a hearingpercept, and an external portion configured to be in wired communicationwith the implantable portion, wherein the electronic components of theimplantable portion are all passive electronic components.

In accordance with another exemplary embodiment, there is a method,comprising accessing a middle ear cavity in a recipient, wherein therecipient includes a cochlea and a tympanic membrane, and implanting anassembly comprising an electrode array of a cochlear implant and anelectrical lead assembly in wired communication with the electrode arrayin a recipient such that the lead assembly extends through the tympanicmembrane and such that the electrode array, which includes a pluralityof electrodes, is implanted in the cochlea such that a plurality ofelectrodes are located in the cochlea, wherein the plurality ofelectrodes are in wired communication with separate respective leads ofthe lead assembly.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the present invention are described below with referenceto the attached drawings, in which:

FIG. 1A is a perspective view of an exemplary hearing prosthesisutilized in some exemplary embodiments;

FIG. 1B is a side view of the implantable components of the cochlearimplant illustrated in FIG. 1A;

FIG. 2 is a side view of an embodiment of the electrode arrayillustrated in FIGS. 1A and 1B in a curled orientation;

FIG. 3A is a functional schematic of an electrode array including 22electrodes spaced apart from one another;

FIG. 3B is a functional block diagram schematic of the system 10 of FIG.1A;

FIG. 4 is a perspective view of an exemplary electric hearing system;

FIGS. 5-8 are functional block diagrams detailing features of variousembodiments;

FIGS. 9-13 are schematics of various lead assembly retention components;

FIGS. 14 and 15 are schematics of circuit portions according toexemplary embodiments;

FIG. 16 is an exemplary functional schematic of an in the ear deviceelectric hearing aid;

FIG. 17 is an exemplary functional schematic of an implantable componentas positioned in the outer, middle and inner ear;

FIG. 18 is an exemplary functional schematic of an in the ear deviceelectric hearing aid; and

FIG. 19 is a flowchart for an exemplary method.

DETAILED DESCRIPTION

FIG. 1A is a perspective view of partially-implantable cochlear implantsystem 10 according to an exemplary embodiment, with a cochlear implant100, implanted in a recipient. The cochlear implant 100 is part of asystem 10 that includes an external component that includes a microphoneand a sound processor. The sound processor processes signals from themicrophone, and generates a signal that is transmitted transcutaneouslyto an implantable component which then uses the signal to stimulatetissue and evoke a hearing percept.

It is noted that in some conventional parlances, the entire system 10 isreferred to as a cochlear implant, especially in the case of a cochlearimplant that is not totally implantable. Herein, the phrase cochlearimplant refers to the implantable component, and the phrase cochlearimplant system refers to the entire system 10. That is, the phrasecochlear implant corresponds to the implantable component of anon-totally implantable cochlear implant system, which in the embodimentof FIG. 1A, includes a receiver-stimulator. It is further noted that thephrase “part of a cochlear implant” refers to a part of such an implant,where that part may or may not be, when used in its totality, a cochlearimplant, unless otherwise specified (analogous to a swing comprisingrope and a wheel of a truck—the wheel must be that of a truck, but it isnot used as part of a truck).

The recipient has an outer ear 101, a middle ear 105, and an inner ear107. Components of outer ear 101, middle ear 105, and inner ear 107 aredescribed below, followed by a description of cochlear implant 100.

In a fully functional ear, outer ear 101 comprises an auricle 110 and anear canal 102. An acoustic pressure or sound wave 103 is collected byauricle 110 and channeled into and through ear canal 102. Disposedacross the distal end of ear canal 102 is a tympanic membrane 104 whichvibrates in response to sound wave 103. This vibration is coupled tooval window or fenestra ovalis 112 through three bones of middle ear105, collectively referred to as the ossicles 106 and comprising themalleus 108, the incus 109 and the stapes 111. Bones 108, 109, and 111of middle ear 105 serve to filter and amplify sound wave 103, causingoval window 112 to articulate, or vibrate in response to vibration oftympanic membrane 104. This vibration sets up waves of fluid motion ofthe perilymph within cochlea 140. Such fluid motion, in turn, activatestiny hair cells (not shown) inside of cochlea 140. Activation of thehair cells causes appropriate nerve impulses to be generated andtransferred through the spiral ganglion cells (not shown) and auditorynerve 114 to the brain (also not shown) where they are perceived assound.

As shown, cochlear implant 100 comprises one or more components whichare temporarily or permanently implanted in the recipient. Cochlearimplant 100 is shown in FIG. 1A with an external device 142, that ispart of system 10 (along with cochlear implant 100), which, as describedbelow, is configured to provide power to the cochlear implant.

In the illustrative arrangement of FIG. 1A, external device 142 maycomprise a power source (not shown) disposed in a Behind-The-Ear (BTE)unit 126. External device 142 also includes components of atranscutaneous energy transfer link, referred to as an external energytransfer assembly. The transcutaneous energy transfer link is used totransfer power and/or data to cochlear implant 100. Various types ofenergy transfer, such as infrared (IR), electromagnetic, capacitive andinductive transfer, may be used to transfer the power and/or data fromexternal device 142 to cochlear implant 100. In the illustrativeembodiments of FIG. 1A, the external energy transfer assembly comprisesan external coil 130 that forms part of an inductive radio frequency(RF) communication link. External coil 130 is typically a wire antennacoil comprised of multiple turns of electrically insulatedsingle-strand/or multi-strand platinum or gold wire or copper wire ortracks on a PCB. External device 142 also includes a magnet (not shown)positioned within the turns of wire of external coil 130. It should beappreciated that the external device shown in FIG. 1A is merelyillustrative, and other external devices may be used with embodiments ofthe present invention.

In some embodiments, external device 142 includes a sound processingunit (not shown) to convert the sound signals received by the microphoneof the BTE unit 126 into signals to be communicated via the inductiveradio frequency communication link to the implanted component.

Cochlear implant 100 comprises an internal energy transfer assembly 132which may be positioned in a recess of the temporal bone adjacentauricle 110 of the recipient. As detailed below, internal energytransfer assembly 132 is a component of the transcutaneous energytransfer link and receives power and/or data from external device 142.In the illustrative embodiment, the energy transfer link comprises aninductive RF link, and internal energy transfer assembly 132 comprises aprimary internal coil 136. Internal coil 136 is typically a wire antennacoil comprised of multiple turns of electrically insulatedsingle-strand/or multi-strand platinum or gold wire.

Cochlear implant 100 further comprises a main implantable component 120and an elongate stimulating assembly 118. In embodiments of the presentinvention, internal energy transfer assembly 132 and main implantablecomponent 120 are hermetically sealed within a biocompatible housing.Main implantable component 120 includes a stimulator unit (also notshown) which generates electrical stimulation signals based on the datasignals. The electrical stimulation signals are delivered to therecipient via elongate stimulating assembly 118.

Elongate stimulating assembly 118 has a proximal end connected to mainimplantable component 120, and a distal end implanted in cochlea 140.Stimulating assembly 118 extends from main implantable component 120 tocochlea 140 through mastoid bone 119. In some embodiments, stimulatingassembly 118 may be implanted at least in basal region 116, andsometimes further. For example, stimulating assembly 118 may extendtowards apical end of cochlea 140, referred to as cochlea apex 134. Incertain circumstances, stimulating assembly 118 may be inserted intocochlea 140 via a cochleostomy 122. In other circumstances, acochleostomy may be formed through round window 121, oval window 112,the promontory 123, or through an apical turn 147 of cochlea 140.

Stimulating assembly 118 comprises a longitudinally aligned and distallyextending array 146 of electrodes 148, disposed along a length thereof.As noted, a stimulator unit generates stimulation signals which areapplied by stimulating contacts 148, which in an exemplary embodimentare electrodes, to cochlea 140, thereby stimulating auditory nerve 114.In an exemplary embodiment, stimulation contacts can be any type ofcomponent that stimulates the cochlea (e.g., mechanical components, suchas piezoelectric devices that move or vibrate, thus stimulating thecochlea (e.g., by inducing movement of the fluid in the cochlea),electrodes that apply current to the cochlea, etc.). Embodimentsdetailed herein will generally be described in terms of a stimulatingassembly 118 utilizing electrodes as elements 148. It is noted thatalternate embodiments can utilize other types of stimulating devices.Any device, system, or method of stimulating the cochlea can be utilizedin at least some embodiments.

Also, while embodiments disclosed herein are directed to electrodes, itis noted that in other embodiments, the teachings detailed herein areapplicable to non-electrical stimulation, such as by way of example onlyand not by way of limitation, mechanical stimulation, opticalstimulation, magnetic stimulation, middle ear acoustic implants (DACS)bone conduction devices, such as active bone conduction devices, etc.Indeed, in an exemplary embodiment, instead of, or in addition, toelectrodes, induction coils are utilized to stimulate the tissue (e.g.,the tissue inside the cochlea). Moreover, it is noted that embodimentsdisclosed herein are not limited to application to hearing prostheses.For example, the teachings detailed herein can be applicable to retinalstimulation, skin stimulation, etc. Further, it is noted that theteachings herein are applicable to stimulating medical devices havingelectrical stimulating electrodes of all types such as straightelectrodes, perimodiolar electrodes and short/basal electrodes. Stillfocusing on a cochlear implant, FIG. 1B is a side view of the cochlearimplant 100 without the other components of system 10 (e.g., theexternal components). Cochlear implant 100 comprises areceiver/stimulator 180 (combination of main implantable component 120and internal energy transfer assembly 132) and an elongate stimulatingassembly 118. Stimulating assembly 118 includes a helix region 182 thatincludes a body 183 in which is embedded (e.g., in the case where thebody is silicone or another biocompatible material molded around wireleads) or otherwise containing (e.g., in the case where the body is aconduit or tube) electrical lead wires 189 in a helix (more on thisbelow), a transition region 184 (which can be part of the body 183), aproximal region 186, and an intra-cochlear region 188. The proximalregion 186, in this embodiment, is connected to the transition region184 via a distinct connection 185, although in other embodiments, thetransition region is blended into the helix region 182 (and the proximalregion 186). Proximal region 186 and intra-cochlear region 188 form anelectrode array 190. The portion of the stimulating assembly 118 thatextends from the receiver/stimulator 180 to the electrode array 190 isreferred to herein as the lead assembly, indicated by reference numeral181 in FIG. 1B. In an exemplary embodiment, proximal region 186 islocated in the middle-ear cavity of the recipient after implantation ofthe intra-cochlear region 188 into the cochlea. Thus, proximal region186 corresponds to a middle-ear cavity sub-section of the stimulatingassembly 118. In some exemplary embodiments, nubs 187 are provided onthe outer surface of the proximal region to aid in the manipulation ofthe electrode array assembly 190 during insertion of the intra-cochlearregion into the cochlea. Electrode array assembly 190, and inparticular, intra-cochlear region 188 of electrode array assembly 190,supports a plurality of electrode contacts 148. These electrode contacts148 are each connected to a respective conductive pathway, such aswires, PCB traces, etc. (not shown) which are connected toreceiver/stimulator 180, through which respective stimulating electricalsignals for each electrode contact 148 travel.

It is noted that in some embodiments, the helix region 182 does notextend as far as that depicted in FIG. 1B, and the transition region 184is thus longer. That is, in some exemplary embodiments, the helix region182 does not extend substantially the full length between thereceiver/stimulator 180 and the proximal region 186, but instead extendsless than that (e.g., about half the distance), where the remainingdistance is established by substantially straight lead wires, or atleast wires that are not substantially helixed. Any arrangement of leadwires that can enable the teachings detailed herein and/or variationsthereof to be practiced can be utilized in some exemplary embodiments.

FIG. 2 is a side view of a portion of stimulating assembly 118 where theelectrode array of the electrode array assembly 190 is in a curledorientation, as it would be when inserted in a recipient's cochlea, withelectrode contacts 148 located on the inside of the curve.

It is noted that FIGS. 1B and 2 can be, by way of example only and notby way of limitation, a lateral wall, a perimodiolar stimulatingassembly or a mid-scala assembly which assumes a mid-scala positionduring or following implantation.

It is noted that the embodiment of FIG. 2 is depicted with a removablestylus 191 that maintains a pre-curved intra-cochlea region of theelectrode array assembly in a more straightened configuration, such thatupon removal of the stylus 191, the intra-cochlea region 188 curls.Embodiments can be practiced with and without the stylus configuration.Embodiments can be practiced with pre-curled arrays and straight arrays.

FIG. 3A illustrates a more detailed view, albeit functionally, of anexemplary electrode array 146 comprising a plurality of electrodes 148labeled 1-22, in accordance with an embodiment. In an exemplaryembodiment, each electrode 148 is an electrode that corresponds to aspecific frequency band channel of the cochlear implant 100, whereelectrode 22 corresponds to the lowest frequency band (channel), andelectrode 1 corresponds to the highest frequency band (channel).Briefly, it is noted that during stimulation by the electrodes to evokea hearing percept, one or more electrodes 148 is activated at a givenelectrode stimulation level (e.g., current level).

The receiver/stimulator 180 of FIG. 1B is an implantable portion of theelectric hearing prosthesis of FIG. 1B. The receiver/stimulator 180 ispresent in the implantable portion because of the transcutaneouscommunication between the implantable component of the hearingprosthesis and the external component wirelessly through the skin of therecipient. In this regard, the external RF coil of the externalcomponent provides signal and/or power to the implantable component viathe implantable coil of the receiver/stimulator unit 180. The stimulatorportion of the receiver/stimulator unit 180 receives the signal from thecoil thereof and converts the signal into stimulation signals that areprovided via the leads 189 to the electrodes so as to electricallystimulate the cochlea to evoke a hearing percept.

Functionally, the components of FIG. 1B are represented in FIG. 3B,along with the external components of the hearing prosthesis system 10.More particularly, element 32 of FIG. 3B represents the BTE device 126of the external portion of the hearing prosthesis of system 10, whereelement 31 represents the sound processor thereof, which processescaptured sound captured by the microphone and ferns that sound intoelectronic signal that are communicated via element 33, which representsthe lead assembly extending from the BTE device 126, to the external RFinductance coil, which coil is represented by element 34. As shown, link35 represents the transcutaneous inductance link between the externalcoil in the implanted coil of the implanted receiver, represented byelement 36. Element 38 represents the implanted stimulator, whichstimulator receive signals from the implanted receiver 36 and convertsthose signals into stimulation signals that are supplied via the leadassembly 181 to the electrode array assembly 190 in general, and theelectrode contacts thereof in particular, so as to stimulate the cochleaand evoke a hearing percept thereby. Collectively, elements 36 and 38represent the receiver/stimulator 180 of the implantable component ofFIG. 1B.

In an alternate embodiment, the receiver portions of thereceiver/stimulator unit 180 are done away with, and the stimulatorportion thereof is located in an external component (if present atall—in other embodiments, stimulation is directly applied from a soundprocessor or the like—more on this below). That is, in an exemplaryembodiment, the implantable portion of the hearing prosthesis caninclude, in its entirety, the portions downrange from thereceiver/stimulator unit 180/the portions to the right of the leadassembly 181 and inclusive of at least a portion of the lead assembly181, and/or some additional ancillary portions (e.g., components to holdthe electrode array assembly 190 in place, a connector potentially,etc.). In an exemplary embodiment, all other portions of the hearingprosthesis are located external to the recipient.

In this vein, FIG. 4 depicts an exemplary embodiment of an electricalhearing prosthesis embodiment that includes an external device 340 thatis part of an external portion of the hearing prosthesis, which cancorrespond to, at least in part, for example, the device of FIG. 1A, butwith additional functionality and/or less functionality and/oradditional features and/or less features as will be described below. Theelectric hearing prosthesis further includes an implantable portion inwired communication with the external device 340, which implantablecomponent includes the electrode array assembly 190, and a portion ofthe body 183 (depending on how much is implanted, more on this below),which can variously correspond to the elongate stimulating assembly 118.

Electrode array assembly 190 is in wired electronic communication withspine 330 of the BTE device 340 via elongate stimulating assembly 118 ingeneral, and the lead wires 189 in particular. In at least someexemplary embodiments, the spine 330 of the BTE contains a soundprocessor/sound processing unit or the like.

Also, in an exemplary embodiment, the spine 330 of the BTE contains astimulator unit that converts the output of the sound processor intosignals that are provided via the lead wires 189 to the electrodecontacts of the electrode array assembly 190. Thus, the stimulatorportion of the cochlear implant of FIG. 1B is located inside otherwiseis part of the external component as opposed to being implanted in therecipient. It is noted that in an exemplary embodiment, the stimulatorunit can be a separate component from the sound processor, while in analternate embodiment, the stimulator unit can be an integral apparatuswith the sound processor.

In this regard, relying on the functional components of FIG. 3B above,FIG. 5 depicts an exemplary functional diagram of the embodiment of FIG.4, wherein element 52 represents the BTE device 126, element 51 againrepresents the sound processor, element 58 represents the stimulator,element 181 represents the lead assembly, an element 190 represents theelectrode array assembly. Thus, the embodiment of FIG. 4 can utilizecomponents of the system 10 in a modified manner so as to operateaccording to the teachings detailed herein. It is further noted that inat least some exemplary embodiments, there is no separate stimulator 58.Instead, the output of the sound processor 51 is sufficient to provide astimulation signal to the electrode contacts of the electrode arrayassembly 190.

BTE device 340 includes one or more microphones 202, and may furtherinclude an audio signal jack 210 under a cover 220 on the spine 330 ofBTE device 340. It is noted that in some other embodiments, one or bothof these components (microphone 202 and/or jack 210) may be located onother positions of the BTE device 340, such as, for example, the side ofthe spine 330, the ear hook 290, etc. FIG. 4 further depicts battery 252and ear hook 290 removably attached to spine 330.

It is noted that while the embodiment of FIG. 4 depicts the microphonebeing located on the spine 330 at about the apex thereof, in analternate embodiment, the microphone can be located elsewhere. It isfurther noted that the microphone can be located on the ear hook 290anywhere from and including the tip thereof to the location where theear hook interfaces with the spine. Such is also the case with respectto the microphone located on the spine 330—the microphone can be locatedanywhere on the spine from the interface of the spine in the ear hook290 to the interface of the battery 252 with the spine 330. Stillfurther, BTE device 575 can include a plurality of microphones locatedaccording to the various teachings detailed herein and/or variationsthereof. Any microphone placement that can enable the teachings detailedherein and/or variations thereof to be practiced can be utilized in atleast some exemplary embodiments.

FIG. 4 depicts a break in the electrical leads extending from spine 330to the electrode array assembly 190. This is depicted for schematicreasons only so as to conserve space, as in at least the embodiment ofFIG. 4, the leads extend uninterrupted from the spine 330 (or moreaccurately, from the connector 332 connected to the spine 330) to theelectrode array assembly 190. Additional details of this will bedescribed below, although it is briefly noted that in an exemplaryembodiment, the portion that is depicted as the break in FIG. 4 cancorrespond to about the location where the lead assembly 181 extendsfrom inside the recipient to the outside of the recipient.

FIG. 6 depicts a functional diagram of a system 50 which corresponds tothe electric hearing prosthesis of FIG. 4 above. For the purposes of thefollowing discussions, reference will be made to functional diagrams forpurposes of linguistic simplicity and economy of language.

More particularly, system 50 includes the electrode array assembly 190,the lead assembly 181, connector 332, and the external device 340, whichcorresponds to the BTE device noted above, where connector 332 placesthe lead assembly 181 into signal communication with the external device340 in general, and the spine 330 of the external device 340 inparticular.

System 50 has been identified in terms of two different sections: animplantable portion 501 and an external portion 502. In the embodimentof FIG. 6, there is no exact demarcation between the implantable portion501 and the external portion 502, while in other embodiments, such asthose that include a stop with the like on the lead assembly 801 (whichstop abuts the tympanic membrane as will be described in greater detailbelow), the implantable portion 501 and the external portion 502 hasmore than exact demarcation between those portions. This is as opposedto considering the system 50 in terms of an implantable component 601and an external component 602, such as seen in FIG. 7, which shows thosecomponent detached from one another (connector 332 has been disconnectedfrom the external device 340). In this regard, the implantable component601, in use, has a portion that is external to the recipient. Thus, animplantable component as that term is used herein does not exclude aportion that is not implanted in use in the recipient. In this regard,the phrase implantable component is a component of the hearingprostheses where at least a portion thereof is configured to beimplanted into a recipient (e.g., the implantable portion 501), and hasstructure that is biocompatible with such. This is as opposed to theconnector 332, which may not necessarily be biocompatible or otherwiseconfigured to be implanted into the recipient, even though it is part ofthe implantable component 601.

In working use, beyond that which results from destructively severingone component from the other, the system 50 can be separated in use asshown in FIG. 7. In particular, the connector 332 is configured torelatively easily connect and disconnect to/from the external device340.

An exemplary embodiment of the system 50 is such that, when theelectrode array assembly 190 is implanted into the cochlea, leadassembly 181 extends through the tympanic membrane to the outside of therecipient, and thus to connector 332, which is connected to the BTEdevice 340. In this regard, all of the active electrical components arelocated outside of the recipient/are located in external portions of theelectric hearing prostheses (the system 50). FIG. 8 functionally depictsportions of a human body superimposed upon the system 50, thusrepresenting a function of version of system 50 and use, or portionthereof is implanted into the recipient. More specifically, blockdiagram 740 represents the cochlea of the recipient, which correspondsto element 140 of FIG. 1A above. Block diagram 706 represents the middleear, and corresponds to elements 106 of FIG. 1A above. Block diagram 704represents the tympanic membrane and corresponds to element 104 of FIG.1A above. Block diagram 702 represents the ear canal/outer ear, and thuscorresponds to element 102 of FIG. 1A above. Line 700 represents theskin of the recipient. In the embodiment of FIG. 8, components to theright of line 700, more accurately, portions of the system 50 to theright of line 700, are implanted in the recipient, and portions to theleft of line 700 are not implanted into the recipient.

Thus, in view of the above, there is a hearing prosthesis, comprising anelectrode array of a cochlear implant, such as electrode array assembly190, configured to be implanted in a cochlea of a recipient. Theprosthesis further includes a lead assembly, such as lead assembly 181,extending from the electrode array, and a connector, such as connector332, located at an end of the lead assembly opposite the electrodearray. The lead assembly is a percutaneous lead assembly in that thelead assembly is configured to extend from outside the skin of therecipient to under the skin of the recipient inside the recipient.Further, the connector is configured to place the lead assembly intowired communication with an external stimulator of the hearingprosthesis, such as external component 340 (whether such uses adedicated stimulator 58 or a sound processor 51 where the signals fromthe sound processor 51 are used to stimulate the electrodes, etc.).

As will be understood from the above, in an exemplary embodiment, thehearing prosthesis includes a BTE device, wherein the connector isconnected to the BTE device as will be described in greater detailbelow, in an alternate embodiment, the prosthesis includes an ITE device(In-The-Ear device), and the connector is connected to the ITE device.In some ITE device embodiments, all of the functionalities of the BTEdevice are present in the ITE device, while in some other ITE deviceembodiments, only some of the functionalities of the BTE device arepresent in the ITE device. In at least some exemplary embodiments, theITE device includes a sound processor and a stimulator (if thestimulator is a separate component from the sound processor) and, insome embodiments, a microphone.

Also as will be understood from the above, in an exemplary embodiment,the hearing prosthesis further includes an external sound processor,such as sound processor 51, wherein the hearing prosthesis does notinclude an RF communication component placing the sound processor intosignal communication with the electrodes of the electrode array. This isbecause with respect to the embodiments detailed above, thetranscutaneous inductance link is done away with, and the electrodearray assembly 190 is in wired communication with the external componentin general, and the sound processor thereof in particular. Note that by“wired communication with the sound processor,” this can include anembodiment where there is no stimulator component interposed between thesound processor and the electrode array assembly, and an embodimentwhere there is a stimulator component interposed between the soundprocessor and the electrode array assembly, the latter being a scenariowhere the electrode array assembly is indirectly in wired signalcommunication with the sound processor.

There can be utilitarian value with respect to fixing the lead assemblyto the skin of the recipient. Such utilitarian value can relate topreventing or otherwise limiting movement of the lead assembly 181, andthus the electrode array assembly 190 relative to the tissue of therecipient. In this regard, in at least some exemplary embodiments,fixing the lead assembly to the skin of the recipient can limit orotherwise prevent movement of the electrode array assembly 190 withinthe cochlea due to, for example, forces acting on the lead assembly 181,which forces can be generated at locations and applied to the leadassembly 181 at locations outside of the recipient relative to thetympanic membrane 104, such as in a scenario where the BTE device 126 istaken off the pinna 110 while still connected to the lead assembly 181and attempted to be moved a distance from the pinna 110 beyond thatwhich would be “permitted” by the lead assembly 181. FIG. 9 depicts anexemplary embodiment of the system 50 utilizing a fixation component910. As can be seen, fixation component/fixation device (sometimesherein referred to as a connector) 910 is a ring extending through thetragus of the outer ear. The lead assembly 181 extends through the ring.In the embodiment depicted in FIG. 9, the portion of the lead assembly181 proximate the ring 910 is fixed to the ring 910 such that the leadassembly 181 cannot move in the longitudinal direction and with thelateral directions beyond that which is permitted by the ring 910. In anexemplary embodiment, the lead assembly 181 is glued to the ring 910. Inan exemplary embodiment, lead assembly 181 is molded around the ring910. In this regard, the body 183 of the lead assembly can be thicker inthe areas proximate to the ring 910, thus permitting the ring to extendthrough a hole in the second area. This concept is seen in FIG. 10,where “extra area” 181E has been added to the sheathing of the leadassembly such that a hole can be present in the extra area 181E throughwhich the ring 910 extends, thus limiting the movement of the leadassembly 181 to the movements of the ring 910 relative to the tragus199. As can be seen, the ring 910 includes a stop at 912 located on thefar side of the ring relative to the viewer's perspective of FIG. 10. Inan exemplary embodiment, a stop can be located on the near side of thering 912 as well. Note also that instead of acting as a stop, element912 can act as the traditional ring closure component of the ring 910.

While the embodiment depicted in FIG. 10 provides a ring that has arelatively large amount of clearance relative to the tragus 199, in analternate embodiment, the general diameter of the ring 910 can besmaller than that depicted in FIG. 10, thus limiting the amount ofclearance relative to the tragus 199. Indeed, as noted above, in anexemplary embodiment, the leads of the lead assembly 181 can passthrough the ring 910, and the ring 910 can create a quasi-compressionfit between the outside of the lead assembly 181 and the skin of therecipient, thus utilizing friction forces to secure the lead assembly181 in place. That said, in an alternate embodiment, this arrangementcan be combined with the embodiment depicted in FIG. 10 and/or inanother arrangement (e.g., where the ring 910 is glued or otherwiseadhered to the lead assembly 181). Any arrangement that will connect thelead assembly 181 to the ring 910 that will limit the movement of thelead assembly 181 so as to have utilitarian value of limiting thelikelihood that the electrode array assembly 190 will be pulled out ofthe cochlea can be utilized in at least some exemplary embodiments.

While the embodiment depicted in FIGS. 9 and 10 are centered around apercutaneous ring, in other embodiments, a clip is utilized that clipsonto the tragus instead of piercing the tragus. Also, instead of a ring,a stud or the like can be utilized. An example of this is depicted inFIG. 12. As shown in FIG. 12, there is a stud 1030 that includes a shaft1020 configured to penetrate the tragus. A screw type or clip type stop1022 is provided at one end of the shaft 1020, and a clip 1030 islocated at the other end of the shaft 1020. In use, the stop 1022 isremoved from the shaft 1020, and the shaft 1020 is inserted through apiercing of the tragus from the ear canal side, such that the clip 1030is located on the far side of the tragus with respect to the view ofFIG. 10. To secure the stud 1030 in place, the stop 1022 is reattachedto the shaft 1020, such that the stop 1022 lies on the outside surfaceof the tragus, and is between the tragus and the viewer with respect tothe frame of reference of FIG. 10. Subsequently to this, the leadassembly 181 is inserted into the inside of the clip 1030, as shown inFIG. 12. Owing to a resiliency of the clip 1030, the clip and grips thelead assembly 181, and thus holds the lead assembly 181 relative to thestud 1030. In other embodiments, adhesive or the like can be utilized tosecure the lead assembly 181 to the stud 1030. Moreover, in someembodiments, the clip 1030 is not utilized, but instead, another stop1022 is utilized in its place, and a second section of the lead assemblyis utilized, analogous to that of FIG. 10. The stud is thus past throughthe hole in the lead assembly 181, and the stop is placed on theopposite side of the shaft 1020 from the tragus, thus trapping the leadassembly 181 between the stop and the tragus.

Any arrangement that can be utilized to secure the lead assembly 181 tothe tragus or other part of the auricle so as to prevent or otherwiselimit the likelihood of the electrode array assembly 190 from beingdislodged from the cochlea as a result of a force applied to the leadassembly 181 beyond the location where the lead assembly is secured canbe utilized.

Note also that while the embodiments depicted above are directed towardssecuring the lead assembly 181 at a location of the outer ear, in anexemplary embodiment, the lead assembly 181 can be secured to tissue ofthe recipient in the middle ear location. In this regard, in anexemplary embodiment, a bone screw and fixture combination can beutilized to secure the lead assembly 181 in the middle ear. An exemplaryembodiment of this is depicted in FIG. 11, where fixture 1130 includes aflanged assembly 1140 having a hole therethrough through which bonescrew 1120 extends, such that the bone screw 1120 can be screwed intobone, trapping the flanged assembly 1140 between the bone and/or skinabove the bone and the head 1122 of the bone screw. As can be seen, theassembly 1140 includes two walls extending 90° away from each other thatseat the lead assembly 181. In the exemplary embodiment depicted in FIG.12, adhesive 1150 is utilized to secure or otherwise attach the leadassembly 181 the assembly 1140. Other types of fixation between the leadassembly 181 and the assembly 1140 can be utilized in other exemplaryembodiments, such as the clip of FIG. 11, etc.

Note also that the embodiment of FIG. 12 can also be utilized in theouter ear instead of the middle ear. A modicum of modification can haveutilitarian value in at least some exemplary embodiments relative to theembodiment utilized in the middle ear. That said, in some alternateembodiments, the fixation device utilized for the middle ear can also beutilized in the outer ear without modification. Note also that in atleast some exemplary embodiments, a fixation device is utilized in themiddle ear and a separate fixation device is utilized in the outer ear.In this regard, the embodiments of FIGS. 10, 11 and/or 12 can becombined in use each securing a different section of the lead assembly181 to the recipient. Note also, in an exemplary embodiment, separatefixtures according to FIG. 12 can be utilized: one in the middle ear,and one in the outer ear.

In view of the above, in an exemplary embodiment, there is a hearingprosthesis as described above and/or below, further comprising aconnector, such as that depicted in FIGS. 10, 11, and/or 12, configuredto retain a portion of the lead assembly relative to the outer ear orthe middle ear when the portion of the lead assembly is located in theouter ear or middle ear, respectively. Still further, in view of theabove, in an exemplary embodiment, there is a hearing prosthesis asdetailed above and/or below, further comprising a connector, such asthat described in the embodiments of FIGS. 10 and 9, configured toconnect a portion of the lead assembly relative to the outer ear whenthe portion of the lead assembly is located in the outer ear viapercutaneous connection to the tragus.

It is also noted that fixation regimes utilized in the middle ear to fixthe electrode array to tissue of the recipient can utilize the ossicles.That is, in an exemplary embodiment, a connector can be connected to theossicles so as to fix the electrode array assembly to the ossicles, thuspreventing the electrode array assembly from moving as a result of aforce applied to the lead assembly in the matters detailed above andvariations thereof. FIG. 13 depicts an exemplary embodiment of aconnector 1330 that can be connected to the ossicles. In an exemplaryembodiment, clip 1322 is malleable, and can be bent around the ossiclesso as to secure support stud 1320 thereto. At the opposite and of stud1320 is clip 1030, which is used in the manner concomitant with thatdetailed above. In this regard, it is also noted that in some alternateembodiments, clip 1030 is also malleable component that can be bent orotherwise deformed about the lead assembly 181 so as to secure the clip1030 to the lead assembly.

Note also that the embodiment of FIG. 13 can be attached to the othercomponents in the middle ear other than the ossicles, such as bonystructures therein that enable the clip 1322 to be attached thereto. Aswith the other connectors detailed herein and variations thereof, theconnector FIG. 13 can be utilized in combination with other connectors,whether such connectors are utilized in the outer ear or the middle ear,etc.

Note also that embodiments can utilize connectors that connect to theouter wall of the cochlea/the interface between the inner here and themiddle ear. Further, as noted above, the electrode array assemblyincludes ridges 197 that enhance the securement of the electrode arrayassembly 190 in the cochlea.

In the embodiment of FIG. 8 and the related embodiments thereof, theembodiments can have utilitarian value in that no parts of theimplantable portion and/or the implantable component of the electrichearing prosthesis are hermetically sealed or otherwise utilize ahermetic enclosure. This is because, with respect to at least some ofthe embodiments detailed herein, such is not needed because all of thecomponents that could be damaged or otherwise experience a deleteriouseffect if exposed to body fluids and/or the internal environment of therecipient are located external to the recipient. This is not to say thatthe components of the implantable portions and/or implantable componentsare not isolated from each other and/or isolated from the ambientenvironment inside the recipient. Standard isolation practices areimplemented. It is that these isolation practices do not correspond tohermetic isolation. In this regard, it is to be understood that one leadis isolated from another lead, and that one electrode contact isisolated from another electrode contact. However, it is that thesecomponents are not hermetically sealed from the ambient environment.This is as opposed to the stimulator of the receiver—stimulator 180 ofthe embodiment of FIG. 1B, where the stimulator 180 will be encased in ahousing that is hermetically sealed from the ambient environment so asto protect the electronic components therein (in some embodiments, thehousing will include feedthroughs to place the lead wires of the leadassembly into electrical communication with the electronic componentslocated inside the housing).

Accordingly, in an exemplary embodiment, there is a hearing prosthesisas detailed herein, wherein there is no hermetic enclosure in any partof the implantable portion and/or implantable component. Indeed, in anexemplary embodiment, there is a hearing prosthesis as detailed hereinwherein there is no hermetic enclosure, even with respect to theexternal portions and/or the external components. In this regard, thehearing prosthesis can be devoid of hermetic enclosures, or at least theimplantable portions and/or implantable components can be devoid ofhermetic enclosures.

As noted above, all of the sound processing componentry and thestimulator componentry are located external to the recipient in at leastsome exemplary embodiments. Thus, in an exemplary embodiment, there isan electric hearing prosthesis, comprising an implantable portionconfigured to electrically stimulate a cochlea to evoke a hearingpercept (e.g., the electrode array assembly 190 and the pertinentportions of the lead assembly 181). This electric hearing prosthesisfurther includes an external portion configured to be in wiredcommunication with the implantable portion (e.g., the portions of thelead assembly 181 located outside the tympanic membrane, the connector332 and the BTE 340 to which the connector is connected. In thisexemplary embodiment, the electronic components of the implantableportion are all passive electronic components. This is as opposed toactive electronic components.

A passive electronic component is a component that does not requireenergy to operate, except for the available alternating current (AC)circuit or direct current (DC) that it is connected to. A passivecomponent is not capable of power gain and is not a source of energy.Generally, passive components are not able to increase the power of asignal nor are they able to amplify the signal. However, they canincrease current or voltage via storage of electrical energy fromresonant frequencies or by a transformer that acts like an electricalisolator. In an exemplary embodiment, the passive circuit, and/or apassive circuit portion (a portion of a circuit) is a lossless circuitand/or a lossless circuit portion, in that it does not have an input oroutput net power flow.

Passive components that use circuit architecture would includeinductors, resistors, voltage and current sources, capacitors, andtransformers. Likewise, passive filters are comprised of four elementarylinear elements that include an inductor, capacitor, resistor, andtransformer. Some high-tech passive filters can have non-linear elementslike a transmission line.

Corollary to the above, in an exemplary embodiment, there is an electrichearing prosthesis, such as any of those detailed herein and/orvariations thereof, that include an implantable component/implantableportion, that is devoid of any integrated circuits. Still further, in anexemplary embodiment, there is an implantable component/portion of anelectric hearing prosthesis that does not include any electronicassemblies.

It is noted that while the passive electronic component teachings abovehave been directed towards the implantable component, these teachingsare also applicable to at least portions of the external portions, suchas the remainder of the lead assembly 181 and the connector 332.

In this regard, FIG. 14 depicts by way of functional diagram a firstcircuit portion 1491 and a second circuit portion 1492 of an exemplaryelectric hearing prosthesis according to some of the embodimentsdetailed herein. Here, the boundaries of the first circuit portion 1491(the dashed box labeled 1491) extend from the connector subcomponents333 for each lead of the connector 332 that interface with respectiveconnector subcomponents 1433 in the external device 340 (to place eachlead into wired electrical communication with corresponding leads orcircuit traces of the external device 340), to and inclusive of theelectrode contacts 1401, 1402, 1403 and 140X (typically, 22 electrodecontacts) of the electrode array assembly 190 (where the electrodecontacts correspond to elements 148 of FIGS. 2B and 2, etc.). The firstcircuit portion also includes the leads 1411, 1412, 1413, and 141X thatrespectively extend from the respective connector subcomponents 333 tothe respective electrode contacts.

Briefly, it is noted that in an exemplary embodiment, the connectorsubcomponents 333 connector prongs that extend into female prongs ofconnector subcomponents 1433 of the external device 340, and thus makeelectrical contact therewith. In some alternate embodiments, theconnector subcomponents 333 are female portions, and the connectorsubcomponents 1433 are male portions. Note also, the combination of thetwo can be utilized, where some of the connector subcomponents 333 aremale and some are female, and vice versa for connector subcomponents1433.

Also as can be seen in FIG. 14, second circuit portion 1492 extends fromand inclusive of the connector subcomponents 1433 to include all othercomponents of the external device 340 (the sound processor 51, thestimulator 58 (if present and distinct from the sound processor 51,etc.).

Also superimposed on the schematic of FIG. 14 is the boundary line 700representing the tympanic membrane. As can be seen, the first circuitportion 1491 extends from inside the recipient to a location outside therecipient.

In view of the above, it is to be understood that in an exemplaryembodiment, the first circuit portion 1491 is a circuit portion that isdevoid of active electronic components. Corollary to this is that theelectronic components of the first circuit portion are all passiveelectronic components. Another way of stating this is that all portionsof the electrical circuit (and/or all portions of the first electriccircuit portion 1491) and/or all portions of the electrical circuitsthat is/are utilized to electrically stimulate the cochlea to evoke andelectric hearing percept that are located inside therecipient/implanted/implantable in the recipient are made up of onlypassive electronic components and do not include any active electroniccomponents. Another way of stating this is that no portion of anyelectrical circuit (and/or no portion of the first electric circuitportion 1491), which portion is implanted in the recipient, includesactive electronic components. Yet another way of stating this is thatany portion of any electrical circuit (and/or any portion of the firstelectric circuit portion 1491), which portion is implanted in therecipient, includes only passive electronic components.

Also, in an exemplary embodiment, it can be said that all portions ofthe electrical circuits located inside the recipient and/or all portionsof the first electric circuit portion 1491 include only electrical leadsand electrode contacts and, if present (e.g., some embodiments can besuch that the electrical leads of the electrical contacts are monolithiccomponents, and thus no bonding is present between the two components),the bonding components that place the electrical leads into wiredcommunication with the electrical contacts, and, if applicable, therespective insulators thereof. This is as distinct from portions of theelectrical circuits that are located outside the recipient (which can bepart of the same circuit of which the implanted portion is a part). Inan exemplary embodiment, it can be said that all portions of theelectrical circuits located inside the recipient (and/or all portions ofthe first electric circuit portion 1491) comprise only conductivecomponents and/or electrically conductive metals and/or metal alloysand, if applicable, the respective insulator components. In an exemplaryembodiment, it can be said that all portions of the electrical circuitslocated inside the recipient (and/or all portions of the first electriccircuit portion 1491) comprise only conductive components and, ifpresent, insulator components.

In an exemplary embodiment, it can be said that all portions of theelectrical circuits located inside the recipient (and/or all portions ofthe first electric circuit portion 1491) do not include resistors (fixedor variable), beyond that which exists naturally owing to the naturalresistance in the electrical leads and/contacts, capacitors, magneticinductive devices, memristors, transducers, antennas, oscillators,and/or any electromechanical devices (all beyond that which might existnaturally owing to the natural features associated with the electricalleads and/or contacts and/or the natural features associated with theelectrical insulation thereof.)

In an exemplary embodiment, it can be said that all portions of theimplantable portions of the electric hearing prosthesis consist orconsist essentially of the lead wires, the material utilized to insulatethe lead wires from one another and from the ambient environment, andany unifying components that hold the lead wires, insulated orotherwise, together, if present, the associated electrode contacts, thesupport for the electrode contacts (e.g., silicone support forming thechassis supporting the electrodes of the electrode array assembly, and,if present, a stylus and, if present, a connector component orcomponents (e.g., as detailed herein).

In an exemplary embodiment, it can be said that all portions of theimplantable portions of the electric hearing prosthesis consist orconsist essentially of conductive metals and/or metal alloys in the formof wires and conductive traces, and non-electronic components (e.g.,silicone supporting the contacts, stylus, the lead chassis, etc.).

FIG. 15 depicts an alternate embodiment where a first electrical circuitportion 1591 extends not from the subcomponents 333 of the connector332, but from the point at which the leads enter the connector 332. Inan exemplary embodiment, this first electrical circuit portion 1591 canextend from the point where the leads first contact the subcomponents333. As can be seen, the second electrical circuit portion 1592 extendsto the point at which the leads enter the connector 332. In an exemplaryembodiment, the second electrical circuit portion 1592 can extend fromthe point where the leads first contact the subcomponents 333. All ofthe teachings detailed herein with respect to the first electricalcircuit portion 1491 and second electrical circuit portion 1492 areapplicable, respectively, to the first electrical circuit portion 1591and the second electrical circuit portion 1592.

In the above, it can be seen that in an exemplary embodiment, all activeelectronic components of the electric hearing prosthesis are part of theexternal portion/external component (e.g., BTE device 340). In anexemplary embodiment, all active electronic components are locatedwithin the second electric circuit portion 1492.

Also in view of the above, it can be seen that in an exemplaryembodiment, the implantable portion of the electric hearing prosthesisincludes a lead assembly (e.g., lead assembly 181) extending from anelectrode array of the implantable portion including a plurality ofelectrodes (e.g., electrode assembly 190), wherein the lead assemblyincludes a plurality of electrically isolated electrical circuitportions (e.g., those portions respectively corresponding to lead wire1411 and contact 1401, lead wire 1412 and contact 1402, lead wire 1413and contact 1403, and lead wire 140X and contact 140X, etc.) extendingfrom a connector (e.g., connector 333) in wired electrical communicationwith the lead assembly to the respective electrodes (contacts 1401,1402, etc.) of the electrode array in a wired manner.

Still further, in an exemplary embodiment of the electric hearingprosthesis, the implantable portion includes a plurality of electricallyisolated circuit portions of the prosthesis each including a respectiveelectrode of an electrode array of the implantable portion. In anexemplary embodiment, this corresponds, respectively, to the lead 1411and contact 1401, etc., of FIG. 14. In this exemplary embodiment, all ofthe respective electrically isolated circuit portions consistessentially of one or more electrical lead portions, an electrode, andelectrical conductivity features between the respective lead portion(s)and the electrodes. As noted above, in an exemplary embodiment, theexternal portion includes a sound processor in one of a BTE or an ITE,and the sound processor is in wired communication with electrodes of anelectrode array of the implantable portion, the electrode array beingconfigured to be placed into a cochlea of the recipient such that aplurality of electrodes are located in the cochlea. This is as opposedto the embodiment of FIG. 1A, where the sound processor is not in wiredcommunication with the electrodes located in the cochlea, but instead isin communication therewith via the transcutaneous RF link.

Also, in an exemplary embodiment, the electric hearing prosthesis issuch that the implantable portion consists of a lead assembly and anelectrode array and/or is such that the implantable component consistsessentially of a lead assembly and an electrode array and an electricalconnector. Also, in an exemplary embodiment, the electric hearingprosthesis is such that the implantable portion consists of a leadassembly and an electrode array and one or more connectors configured toconnect the lead assembly to tissue of the recipient and/or is such thatthe implantable component consists of or consist essentially of a leadassembly and an electrode array and an electrical connector and one ormore connectors configured to connect the lead assembly to tissue of therecipient. Moreover, in an exemplary embodiment, the electric hearingprosthesis is such that the implantable portion is a portion only madeup of components selected from the group consisting of a lead assembly,an electrode array and one or more connectors configured to connect thelead assembly to tissue of the recipient. In an exemplary embodiment,the electric hearing prosthesis is such that the implantable componentis a component made up of only components selected from the groupconsisting of a lead assembly an electrode array (which can include astraightening element, such as a stylus or a sheath), an electricalconnector, one or more fixation devices (such as a connector) configuredto connect the lead assembly to tissue of the recipient, and an activeelectronics package (located between connector 332 and the electrodearray assembly, and electrodes 1401 etc., in particular, in the externalportion (as opposed to the implantable portion) of the implantablecomponent). With respect to the latter, as will be detailed below, adevice, such as component 1632 as will be described in greater detailbelow, can be utilized such that signals from a limited number ofcontacts from the sound processor (e.g., 3 or 4 or so—an amount morethan or equal to 3 or 4 or 5 or 6 or 7 or 8 times less than the numberof electrodes of the electrode array assembly) can be analyzed by thethe active electronics package to assign stimulation signals to the 22electrodes (or however many there are) of the electrode array assembly.

In some exemplary embodiments, the implantable portion is part of animplantable component (e.g., component 601). The implantable componentconsists of an assembly of components selected from the group consistingof (i) a connector (e.g., element 332) configured to connect to anexternal component of an external portion of the prosthesis containingactive electronic components (e.g., external device 340 of externalcomponent 602), (ii) electrodes (e.g., contacts 148), (iii) respectiveleads extending from the respective electrodes to the connector (e.g.,lead wires 189), (iv) respective insulator components for the leadsand/or electrodes and/or respective support components for the leadsand/or electrodes (e.g., the insulators of the leads, the silicone ofthe electrode array assembly (sometimes referred to as an electrodecarrier), etc., (v) one or more fixation devices configured to connectthe implantable portion to tissue of the recipient (e.g., any of theconnectors of FIGS. 9-13, (vi) body interface portions configured tointerface the support components with tissue of the recipient (e.g.,groves 197), (vii) a stylus (e.g., element 191, if present) and/or asheath, (viii) the active electronics package noted above and furtherdetailed below, and (ix) electrode positioning maintenance components(e.g., stiffening structures located in the electrode array assembly).

In view of the above, it is to be understood that in an exemplaryembodiment, the hearing prosthesis includes an external sound processorin wired signal communication with the electrodes of the electrodearray. Further, the external sound processor is part of an externalportion of the hearing prosthesis, the electrode array is part of animplantable portion of the hearing prosthesis, and the implantableportion of the hearing prosthesis is devoid of active electroniccomponents.

As noted above, some exemplary embodiments are utilized with externalcomponents that include in the ear (ITE) devices instead of and/or inaddition to behind the ear (BTE) devices. In this regard, FIG. 16functionally depicts an exemplary embodiment of a system of an electrichearing prosthesis that utilizes an ITE device, along with functionalrepresentations of the pertinent portions of the anatomy of therecipient. In this regard, the frame of reference of FIG. 16 correspondsto that of FIG. 8 detailed above with respect to the BTE device. Here,ITE device 1640 is connected via connector 1638 to connector 1632 whichis connected to lead assembly 181. As can be seen, the connector 1632 islocated inside the ear canal 702. Here, the implantable portion 501corresponds to that detailed above, but the external portion correspondsto those elements making up portion 1602. That said, the implantablecomponent will correspond to connector 1632, lead assembly 181, anelectrode array assembly 190, whereas the external component willcorrespond to the ITE device 1640, the connector 1638, and the lead (notlabeled) connecting the connector 1638 to the ITE device 1640. It isnoted that in an alternate embodiment, the connector 1638 can be hardmounted to the ITE device 1640. That is, the connector 1638 can be anintegral part of the ITE device 1640. Corollary to this is that in anexemplary embodiment, the connector of the BTE device detailed above canbe a component that is located remote from the BTE device and connectedthereto via a lead in a manner consistent with the teachings of FIG. 16,albeit as modified to accommodate the utilization of a BTE deviceinstead of an ITE device. In an exemplary embodiment, the implantableportion 501 corresponds to the portion of the elongate simulativeassembly of the Nucleus 5™ cochlear implant manufactured by Cochlear LTDof Australia and implanted into recipients in the United States pursuantto approval of the FDA in the years 2014, 2015, or 2016, located about1.0, 1.5, 2.0, 2.5, 3.0, 3.5, or 4 inches away from thereceiver/stimulator thereof to the distal end of the electrode array.

As briefly mentioned above, some exemplary embodiments utilize a stopdevice or the like that interfaces with the tympanic membrane so as toprevent movement of the lead assembly 181 relative to the tympanicmembrane. In this regard, FIG. 17 depicts an exemplary embodiment by wayfunctional representation, where a stop at 1710 is located about theelectrode array 181, which stop abuts the outside of tympanic membrane704 and prevents migration of the lead assembly 181 into the middle earcavity 76. Alternatively, and/or in addition to this, a stop can belocated about the electrode array 181, which stop abuts the inside ofthe tympanic membrane 704, and prevents migration of the lead assembly181 out of the middle ear cavity 706. Of note is that of FIG. 17 depictsthe lead assembly 181 extending to the tympanic membrane at an outerperiphery thereof. There can be utilitarian value with respect toinserting the lead assembly through and/or otherwise puncture in thetympanic membrane at the periphery thereof as opposed to a more centrallocation. In this regard, by way of example only and not by way oflimitation, with respect to recipients that have residual hearing,locating the lead assembly 181 away from the central portion of tympanicmembrane will permit the tympanic membrane to flex or otherwise vibratein a more normal manner relative to that which would be the case if thelead assembly 181 extended through the center thereof or portionsproximate the center thereof. In this regard, to the extent that thelead assembly 181 has a dampening effect on the tympanic membrane as aresult of its extension therethrough, the dampening effect is lessenedif the lead assembly 181 is located at the other periphery of thetympanic membrane.

Accordingly, in an exemplary embodiment, there is electric hearingprosthesis, wherein the hearing prosthesis includes a stop portionconfigured to interface with the tympanic membrane so as to secure aportion of the implantable portion relative to the tympanic membrane.

In an exemplary embodiment, the stop portion can be a spherical beadthat extends about the lead assembly 181. This spherical bead can beintegral with the lead assembly 181 (e.g., it can be an extension of theinsulative material around the lead wires/a bulge in the insulativematerial, akin or otherwise analogous to element 181E of FIG. 10). Thisspherical bead can be separate from the lead assembly 181, andmechanically and/or chemically attached thereto. Alternatively, and/orin addition to this, the stop can be a flat circular plate or a squareplate etc., through which the lead assembly 181 extends. This plate canalso be integral with the lead assembly 181, concomitant with the beaddetailed above. The plate can have features that change position whenpassing through a hole in the tympanic membrane. For example angledprotrusions which push flat against the lead when passing through a holeand spring out to form a stop.

In an exemplary embodiment, a clip like device or the like can be placedon or about the lead assembly 181 after the lead assembly 181 isextended through the tympanic membrane/the hole in the tympanic membraneplaced therein during the surgery procedure (more on this below). Inthese embodiments, the stop is fixed to the lead assembly such that thelead assembly will not move without the stop moving as well, barringsome form of destructive deformation of the assembly. Thus, the stopwill fix the lead assembly relative to the tympanic membrane providingthat the stop cannot move relative to the tympanic membrane, at least inone direction.

With reference back to FIGS. 16 and 17, it is noted that there can beutilitarian value with respect to utilizing a multiplexing regime or thelike vis-à-vis placing the leads of the lead assembly 181 into wiredcommunication with the external device in the form of an ITE device. Inthis regard, the connector 1632 and/or 1638 are configured to be locatedin the ear canal 702 of the recipient. This is a relatively tiny area inwhich the connector is to be located, which connector can have 22 ormore separate sub-connection components (one for each of the 22 leadsfor the respective 22 electrodes, plus one or more leads for the returnelectrodes). This could result in 23 or 24 or more separate connectionsthat should be electrically isolated from one another. Accordingly,there can be utilitarian value with respect to reducing the number ofseparate connections to be electrically isolated from one another, thusreducing the size of the connector 1632 and/or 1638. In this regard,FIG. 18 depicts an exemplary system that utilizes a connector 1832 thatis part of the implantable component (where the connector of the ITEdevice 1640 is an integral part thereof), which also includes amultiplexer component 1839. In this exemplary embodiment, the connector1832 includes no more than 2 or 3 or 4 or 5 or 6 or 7 or 8 or 9 or 10 or11 or 12 or 13 separate sub-connector components, depending on theembodiment. Multiplexer 1839 receives signals from these sub-connectorcomponents, and analyzes these signals and break them up and otherwisedivides the signals into respective signals for the respective leads ofthe lead assembly 181.

In an alternate embodiment, instead of the utilization of hardwiredconnectors, a very short range but high-efficiency RF link is utilizedto communicate between IT device 1640 and the implantable component. Byway of example only and not by way of limitation, element 1638 caninstead be a high-efficiency RF transmitter and element 1632 can be ahigh-efficiency RF receiver. Moreover, in an exemplary embodiment,element 1632 can include a stimulator device. In this regard, by way ofexample only and not by way of limitation, element 1632 can functionaccording to the receiver/stimulator 180 detailed above, an element 1638can function according to the RF transmitter of the embodiment of FIG.18 detailed above. Such can have utilitarian value with respect toreducing (in this embodiment, eliminating) the need for sub-connectorcomponents which could crowd or otherwise be difficult to implement inthe limited space within the ear canal 702.

FIG. 19 presents an exemplary flowchart for an exemplary method, method1900, according to an exemplary embodiment. Method 1900 includes methodaction 1910, which entails accessing a middle ear cavity in a recipient.As will be detailed below, in an exemplary embodiment, this entailscreating an artificial opening in the tympanic membrane such that themiddle ear cavity can be accessed from the ear canal of the recipient.Method 1900 further includes method action 1920, which entailsimplanting an assembly comprising an electrode array (e.g., electrodearray assembly 190) of a cochlear implant and an electrical leadassembly (e.g., lead assembly 181) in wired communication with theelectrode array in a recipient such that the lead assembly extendsthrough the tympanic membrane and such that the electrode array, whichincludes a plurality of electrodes, is implanted in the cochlea suchthat a plurality of electrodes are located in the cochlea, wherein theplurality of electrodes are in wired communication with separaterespective leads of the lead assembly. By way of example only and not byway of limitation, in an exemplary embodiment, the electrode arrayincludes at least 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20,21, or 22, or more electrodes. In an exemplary embodiment, all of theelectrodes of the electrode array are located in the cochlea as a resultof method action 1920. In an exemplary embodiment, only a subset of theelectrode array located in the cochlea as a result of method action1920, which subset includes a plurality of electrodes.

In an exemplary embodiment, method 1900 further comprises the action ofcompleting the implantation of the assembly without drilling into boneof the recipient. By way of example only and not by way of limitation,method 1900 instead comprises the action of completing the implantationof the assembly without drilling into the mastoid bone and/or temporalbone of the recipient. That said, in an exemplary embodiment, method1900 instead comprises the action of completing the implantation of theassembly without drilling into bone of the recipient other than holesfor fixation screws used to attach portions of the lead assembly totissue of the recipient and/or other than fixation passageways for clipsor the like used to attach portions of the lead assembly to tissue ofthe recipient. By way of example only and not by way of limitation, sucha fixation screw can correspond to the fixation screw 1120 of FIG. 12above. Still further by way of example only and not by way oflimitation, such clips can correspond to the clip of FIG. 13 above.

In an exemplary embodiment, method 1900 further includes the action ofcreating an artificial opening in the tympanic membrane. Indeed, in anexemplary embodiment, this action corresponds to the action of accessinga middle ear cavity in the recipient (method action 1910). In anexemplary embodiment, the opening in the tympanic membrane isconcomitant with an opening created for drainage grommets in surgeriesfor people who require drainage or drying of fluid out of the middle earor otherwise require pressure relief from the middle ear cavity throughthe tympanic membrane to the ambient environment. By way of example onlyand not by way of limitation, the opening created is about 1.5 mm inmaximum diameter. In an exemplary embodiment, the opening created isabout 1 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8mm, 1.9 mm, 2 mm, 2.1 mm, or 2.2 mm in maximum diameter. In an exemplaryembodiment, the entire electrode array assembly 190 is fed through thisartificial opening from the outer ear into the middle ear cavity.Indeed, prior to this, a cochleostomy or an opening in the round windowor the oval window of the cochlea is performed through this incision inthe tympanic membrane, or more accurately, the tools that are utilizedto create the opening in the cochlea are inserted through the incisionin the tympanic membrane, and manipulated by mechanical extensionthrough the insertion of the tympanic membrane so as to create therequisite opening in the cochlea so as to extend the electrode arraytherethrough. In this regard, method 1900 can be considered a minimallyinvasive surgical procedure, at least relative to a conventionalcochlear implant implantation.

Accordingly, in an exemplary embodiment, method 1900 includes the actionof inserting the electrode array through the incision in the tympanicmembrane, followed by inserting the implantable portion of the leadassembly through the tympanic membrane. Corollary to this is that method1900 includes the action of inserting the electrode array into thecochlea by manipulating the electrode array utilizing tools extendingthrough the incision of the tympanic membrane. Thus, an exemplaryembodiment of method 1900 further includes the action of making anartificial incision in the tympanic membrane, extending the electrodearray through the artificial incision, after extending the electrodearray through the artificial incision, inserting the electrode arrayinto the cochlea such that the plurality of electrodes are inserted intothe cochlea. In this exemplary embodiment, the electrode array ismanipulated via forces directed through the artificial incision in thetympanic membrane.

That said, in some alternate embodiments, an incision through the skinof the recipient located away from the ear canal approximate thereto iscreated so as to access the middle ear. In this exemplary embodiment,instead of moving the electrode array and/or the lead assembly throughan incision in the ear canal, the electrode array and/or the leadassembly is moved through this incision which bypasses the ear canal. Inan exemplary embodiment, the middle ear of the recipient can be reachedwithout drilling into bone. This includes accessing the middle ear byelevating the skin of the ear canal and passing the electrode arrayunder the skin.

Because the embodiments detailed herein can be implemented via extensionof the electrode array and the associated lead assembly into the middleear and thus into the cochlea from the outer ear in general, and the earcanal in particular, or from around the outer ear but through the skinof the recipient into the middle ear cavity, some exemplary embodimentsof method 1900 can be executed utilizing only local anesthetics. Thatis, by way of example only and not by way of limitation, method 1900 issuch that the implantation is executed on a recipient under only localanesthetics, which recipient is not suffering from any other ailmentbeyond a hearing defect. That is, all things being equal, the recipienthas a physiological state both chronically and acutely vis-à-vis thetime of the surgery that, all things being equal, would not prevent therecipient from being sedated with anesthesia that effectively “knocksout” the patient, anesthesia beyond local anesthetics. This is asopposed to a physiological state that would prevent the recipient frombeing provided such anesthesia. In an exemplary embodiment, by way ofexample only and not by way of limitation, the recipient (patient) is apatient that would be mandated by the FDA in the United States to beplaced under full anesthesia for a traditional cochlear implant surgery.In an exemplary embodiment, by way of example only and not by way oflimitation, the recipient is a person less than 3 years of age, 3 yearsto 12 years of age, 12 years to 18 years of age, 18 years to 65 years ofage, or 65 years and older in age, who is a 10^(th) percentile to90^(th) percentile person health-wise for that age group save for thehearing deficiencies warranting the method 1900.

Consistent with the teachings detailed above vis-à-vis the connectorsused to connect the lead assembly to the external component, in anexemplary embodiment, the lead assembly utilized in method 1900 includesat least 7 separate lead wires respectively connected to at least 7separate electrodes of the electrode array, wherein all 7 separateelectrodes are inserted into the cochlea. That said, in an exemplaryembodiment, the lead assembly utilized in method 1900 includes at least8 leads and electrodes, 9 leads and electrodes, 10 leads and electrodes,11 leads and electrodes, 12 leads electrodes, 13, 14, 15, 16, 17, 18,19, 20, 21, or 22, or more leads and electrodes, where the respectiveleads are respectively connected to the respective separate electrodes.Still further, a connector is connected to the lead assembly. In anexemplary embodiment, method 1900 further comprises, after the action ofimplanting the assembly, connecting an external device to the connectorat a location outside the tympanic membrane relative to the middle earand the inner ear of the recipient. By way of example only and not byway of limitation, this external device is an ITE or a BTE device asdetailed above.

Still further, in an exemplary embodiment of method 1900, method 1900further includes the action of fixing the electrical lead assembly totissue of the recipient. In an exemplary embodiment, this is executedutilizing the devices, systems, and methods detailed above with respectto FIGS. 9 to 13. That said, in an alternate embodiment, suturing or thelike is utilized. Indeed, in an exemplary embodiment, the lead assembly181 can be sutured to the inner wall of the ear canal. In an exemplaryembodiment, the lead assembly 181 can be sutured to tissue, and/or bone,within the middle ear cavity of the recipient. Moreover, the leadassembly 181 can be sutured to the tragus of the ear, instead of or inaddition to utilizing the ring system of FIG. 10 or the like. Anydevice, system, or method of securing a portion of the lead assembly totissue of the recipient so as to prevent migration or otherwise so as toprevent a force imparted on the lead assembly 181 from dislodging theimplant electrode array can be utilized in at least some exemplaryembodiments.

Concomitant with the teachings detailed above with respect to placingonly passive components in the recipient, and maintaining all activecomponents in external portions of the hearing prosthesis, in anexemplary embodiment, method 1900 further comprises completingimplantation of all implantable portions of an electric hearingprosthesis such that no active electronic components are implantedinside the recipient. Corollary to this is that in an exemplaryembodiment, method 1900 further comprises completing implantation of allimplantable portions of the electric hearing prosthesis such that withrespect to the electronic components of the hearing prosthesis, onlypassive electronic components are implanted inside the recipient.

Note also that instead of, or in addition to, the utilization of thefixation devices, systems, methods detailed herein that are utilized tofix the lead assembly to tissue of the recipient, and exemplaryembodiment entails providing excess lead assembly in the outer earand/or in the middle ear beyond that which is needed to extend the leadassembly from the electrode array, once fully implanted, to an externalcomponent to which the lead assembly is to be placed into wiredcommunication. By way of example only and not by way of limitation, thiscan entail providing a loop or a wave slacking in the portion of thelead assembly located in the middle ear. Still further by way of exampleonly and not by way of limitation, alternatively and/or in addition tothis, this can entail providing a loop or a wave slacking in the portionof the lead assembly located in the ear canal.

In an exemplary embodiment, there is a hearing prosthesis as describedabove and/or below, wherein the hearing prosthesis includes an externalsound processor in wired signal communication with the electrodes of theelectrode array, the external sound processor is part of an externalportion of the hearing prosthesis, the electrode array is part of animplantable portion of the hearing prosthesis, and the implantableportion of the hearing prosthesis is devoid of active electroniccomponents.

In an exemplary embodiment, there is a hearing prosthesis as describedabove and/or below, wherein the hearing prosthesis includes a stopportion configured to interface with the tympanic membrane so as tosecure a portion of the implantable portion relative to the tympanicmembrane.

In an exemplary embodiment, there is a hearing prosthesis as describedabove and/or below, wherein the implantable portion is part of animplantable component, the implantable component consisting of anassembly of components selected from the group consisting of (i) aconnector configured to connect to an external component of an externalportion of the prosthesis containing active electronic components, (ii)electrodes, (iii) respective leads extending from the respectiveelectrodes to the connector, (iv) respective insulator components forthe leads and/or electrodes and/or respective support components for theleads and/or electrodes, (v) a fixation device configured to connect theimplantable portion to tissue of the recipient, (vi) body interfaceportions configured to interface the support components with tissue ofthe recipient, (vii) a stylus, and (viii) electrode positioningmaintenance components. In an exemplary embodiment, there is a hearingprosthesis as described above and/or below, wherein the external portionincludes at least one of: an RF transmitter and an RF receiver; or adevice configured to expand a first number of signal channels to asecond number of signal channels greater than the first number of signalchannels.

In an exemplary embodiment, there is a method as described above,further comprising providing excess lead assembly in a middle ear and inthe outer ear of the recipient beyond that which is needed to extend thelead assembly from the electrode array to an external component to whichthe lead assembly is to be placed into wired communication.

It is noted that any disclosure of any method of making any componentherein corresponds to a disclosure of the resulting component. It isfurther noted that any disclosure of any method action hereincorresponds to a disclosure of an apparatus configured to execute suchdisclosure. Is also noted that any disclosure of any apparatus and/orsystem herein corresponds to a method of utilizing and/or making such.Any feature of any embodiment detailed herein can be combined with anyother feature of any other embodiment detailed herein, unless otherwisespecifically noted to the contrary.

While various embodiments of the present invention have been describedabove, it should be understood that they have been presented by way ofexample only, and not limitation. It will be apparent to persons skilledin the relevant art that various changes in form and detail can be madetherein without departing from the scope of the invention.

What is claimed is:
 1. An electric hearing prosthesis, comprising: animplantable portion configured to electrically stimulate a cochlea toevoke a hearing percept; and an external portion configured to be inwired communication with the implantable portion, wherein electroniccomponents of the implantable portion are all passive electroniccomponents, the external portion includes one or more sound capturedevice(s), and the electrical hearing prosthesis includes a devicedownstream from the one or more sound capture device(s) configured toexpand a first number of signal channels to a second number of signalchannels greater than the first number of signal channels.
 2. Theelectric hearing prosthesis of claim 1, wherein: the external portionincludes a sound processor in an in the ear device; the sound processoris in wired communication with electrodes of an electrode array of theimplantable portion, the electrode array being configured to be placedinto a cochlea of the recipient such that a plurality of electrodes arelocated in the cochlea, the wired communication being via an assemblythat extends from the in the ear device down an ear canal towards themiddle ear and then to the electrode array; and the prosthesis isconfigured such that signals from a limited number of contacts from thesound processor is analyzed to assign stimulation signals to a number ofelectrodes greater than the limited number of contacts, the electrodesbeing configured to stimulate tissue of a person to evoke a hearingpercept.
 3. The electric hearing prosthesis of claim 1, wherein: thehearing prosthesis includes a stop portion configured to interface withthe tympanic membrane so as to secure a portion of the implantableportion relative to the tympanic membrane.
 4. The electric hearingprosthesis of claim 1, wherein: the electric hearing prosthesis includesan external sound processor in wired signal communication withelectrodes of the implantable portion, which electrodes are configuredto electrically stimulate the cochlea to evoke the hearing percept; theexternal sound processor is part of an external portion of the electrichearing prosthesis; the implantable portion is devoid of activeelectronic components.
 5. The electric hearing prosthesis of claim 1,wherein the external portion includes an external sound processor,wherein the electric hearing prosthesis does not include an RFcommunication component placing the sound processor into signalcommunication with electrodes of the implantable portion, whichelectrodes are configured to electrically stimulate the cochlea to evokethe hearing percept.
 6. The electric hearing prosthesis of claim 1,wherein: the external portion includes the device downstream from theone or more sound capture device(s) configured to expand a first numberof signal channels to a second number of signal channels greater thanthe first number of signal channels.
 7. The electric hearing prosthesisof claim 1, wherein: the implantable portion includes a tissuestimulating component configured to stimulate ear tissue to evoke ahearing percept; a percutaneous lead assembly extends from tissuestimulating component to the external portion; a connector connects afirst length of the lead assembly extending from the tissue stimulatingcomponent to a second length of the lead assembly extending from anexternal functional component of the external portion, the connectorbeing configured to releasable connect the first length to the secondlength; and the hearing prosthesis is configured such that the connectoris located in an ear canal when the tissue stimulating component isimplanted at a location in the recipient to stimulate the ear tissue andthe electric hearing prosthesis is used to evoke a hearing percept. 8.The electric hearing prosthesis of claim 1, wherein: the externalportion includes an in the ear canal device; all external portions areconfigured to be located in an ear canal of a recipient; and a connectorconnects a first length of a lead assembly extending from a tissuestimulating device of the hearing prosthesis to a second length of thelead assembly extending from the in the ear canal device, the connectorbeing configured to releasable connect the first length to the secondlength.
 9. The electric hearing prosthesis of claim 1, wherein: theimplantable portion includes a tissue stimulating component configuredto stimulate tissue to evoke a hearing percept; a percutaneous wireextends from tissue stimulating component to the external portion; aconnector distinct from the wire, the connector connecting a firstlength of the wire extending from the tissue stimulating component to asecond length of the wire extending from an external functionalcomponent of the external portion, the connector being configured toreleasable connect the first length to the second length; and thehearing prosthesis is configured such that the connector is located inan ear canal when the tissue stimulating component is implanted at alocation in the recipient to stimulate the ear tissue and the electrichearing prosthesis is used to evoke a hearing percept.
 10. The electrichearing prosthesis of claim 1, wherein: the implantable portion consistsof wire(s) and an electrode array.
 11. An electric hearing prosthesis,comprising: an implantable portion configured to electrically stimulatea cochlea to evoke a hearing percept; and an external portion configuredto be in wired communication with the implantable portion, whereinelectronic components of the implantable portion are all passiveelectronic components, and wherein the implantable portion includes atissue stimulating component configured to stimulate ear tissue to evokea hearing percept; an RF transmitter is in wired signal communicationwith a functional component of the external portion; an RF receiver isin wired signal communication with the tissue stimulator component; andthe hearing prosthesis is configured such that the RF transmitter andthe RF receiver are fitted into an ear system of a recipient when therecipient is using the prosthesis to evoke a hearing percept.
 12. Theelectric hearing prosthesis of claim 11, wherein: the implantableincludes an electrode array of a cochlear implant, the prosthesisincludes a lead assembly that is a percutaneous lead assembly andextends from the electrode array, and a connector is located at an endof the lead assembly opposite the electrode array such that theconnector is supported by only the lead relative to the recipient of thecochlear implant.
 13. The electric hearing prosthesis of claim 11,wherein: the implantable includes an electrode array of a cochlearimplant, the prosthesis includes a lead assembly that is a percutaneouslead assembly and extends from the electrode array, and a connector islocated at an end of the lead assembly opposite the electrode array suchthat the entire connector is completely outside a recipient of thecochlear implant when the electrode array is implanted in the cochlea.14. The electric hearing prosthesis of claim 11, wherein: the prosthesisincludes a multiplexer component configured to be located in the earsystem.
 15. The electric hearing prosthesis of claim 14, wherein: themultiplexer receives signals from a first number of leads, and analyzesthese signals and breaks the signals up and/or divides the signals upinto respective signals for respective second number of leads which leadto the tissue stimulating component, the second number of leads being atleast twice the first number of leads.
 16. The electric hearingprosthesis of claim 11, wherein: the hearing prosthesis is configuredsuch that the RF transmitter and the RF receiver are fitted into an earcanal of a recipient when the recipient is using the prosthesis to evokea hearing percept, the RF transmitter providing a wireless signal to theRF receiver to evoke a hearing percept.
 17. The electric hearingprosthesis of claim 11, wherein: a percutaneous lead assembly extendsfrom tissue stimulating component to the external portion; a connectorconnects a first length of the lead assembly to a second length of thelead assembly; and the connector includes a multiplexer component. 18.An electric hearing prosthesis, comprising: an implantable portionconfigured to electrically stimulate a cochlea to evoke a hearingpercept; and an external portion configured to be in wired communicationwith the implantable portion, wherein the hearing prosthesis isconfigured such that the only portion that extends from supercutaneouslocations to subcutaneous locations extends through a tympanic membraneof a recipient of the prosthesis when the hearing prosthesis isimplanted in a recipient, and the electric hearing prosthesis furthercomprises: a sound processor that is part of the external portion; and adevice configured such that signals from a limited number of contactsfrom the sound processor is analyzed to assign stimulation signals to anumber of electrodes greater than the limited number of contacts, theelectrodes being configured to stimulate tissue of a person to evoke ahearing percept.
 19. The electric hearing prosthesis of claim 18,wherein: the implantable portion includes a plurality of electricallyisolated circuit portions of the prosthesis each including a respectiveelectrode of an electrode array of the implantable portion; and all ofthe respective electrically isolated circuit portions of the implantableportion consist essentially of one or more electrical lead portions, anelectrode, and electrical conductivity features between the respectivelead portion(s) and the electrodes.
 20. The electric hearing prosthesisof claim 18, wherein: the implantable portion consists of a leadassembly and an electrode array.
 21. The electric hearing prosthesis ofclaim 18, wherein: the implantable portion is an electrode array of acochlear implant, a lead assembly is a percutaneous lead assembly andextends from the electrode array to the external portion, and the leadassembly is configured such that a portion of the lead assembly extendscompletely out of an ear canal of the via a supercutaneous route to alocation behind a pinna of the recipient.
 22. The electric hearingprosthesis of claim 18, wherein: the external portion includes an in theear canal device; all external portions are configured to be located inan ear canal of a recipient; a connector connects a first length of awire, extending from a tissue stimulating device of the hearingprosthesis to the connector, to a second length of a wire extending fromthe in the ear canal device to the connector, the connector beingconfigured to releasable connect the first length to the second length.